EP2724319B1 - Respiratory motion determination apparatus - Google Patents

Respiratory motion determination apparatus Download PDF

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Publication number
EP2724319B1
EP2724319B1 EP12735044.5A EP12735044A EP2724319B1 EP 2724319 B1 EP2724319 B1 EP 2724319B1 EP 12735044 A EP12735044 A EP 12735044A EP 2724319 B1 EP2724319 B1 EP 2724319B1
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respiratory
respiratory motion
raw data
image
images
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English (en)
French (fr)
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EP2724319A1 (en
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Sven Kabus
Hans-Aloys Wischmann
Cristian Lorenz
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Philips Intellectual Property and Standards GmbH
Koninklijke Philips NV
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Philips Intellectual Property and Standards GmbH
Koninklijke Philips NV
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1126—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb using a particular sensing technique
    • A61B5/1128—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb using a particular sensing technique using image analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/037—Emission tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
    • A61B6/5264—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to motion
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5288—Devices using data or image processing specially adapted for radiation diagnosis involving retrospective matching to a physiological signal
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/0002—Inspection of images, e.g. flaw detection
    • G06T7/0012—Biomedical image inspection
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/0002—Inspection of images, e.g. flaw detection
    • G06T7/0012—Biomedical image inspection
    • G06T7/0014—Biomedical image inspection using an image reference approach
    • G06T7/0016—Biomedical image inspection using an image reference approach involving temporal comparison
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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61B2576/00—Medical imaging apparatus involving image processing or analysis
    • A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part
    • A61B2576/023—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
    • A61B5/352—Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
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    • G06T2207/10072—Tomographic images
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    • G06T2207/30004—Biomedical image processing
    • G06T2207/30061—Lung
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H30/00—ICT specially adapted for the handling or processing of medical images
    • G16H30/40—ICT specially adapted for the handling or processing of medical images for processing medical images, e.g. editing

Definitions

  • the invention relates to a respiratory motion determination apparatus, a respiratory motion determination method and a corresponding computer program for determining respiratory motion of a living being.
  • US 2008/0240536 A1 discloses a system that synchronizes two-dimensional x-ray projection images, i.e. radiography images, of a heart with an electrocardiogram, in order to eliminate motion related to the heart cycle from these images. After the motion related to the heart cycle has been eliminated, the motion in the x-ray projection images is respiratory motion only. The system detects the respiratory motion in these x-ray projection images and uses the detected respiratory motion for improving a registration between the x-ray projection images and a pre-acquired three-dimensional image of the heart.
  • two-dimensional x-ray projection images i.e. radiography images
  • electrocardiogram electrocardiogram
  • WO 2011/070465 A2 discloses calculating a center of activity for each of several respiratory gated cardiac images, wherein differences regarding the position of the center of activity in the different respiratory gated cardiac images are used to generate respiratory motion vectors, which are used to correct list mode data for respiratory motion in image reconstruction.
  • US 2008/0226149 A1 discloses using a respiratory motion sensor as an external device for determining respiratory phases, wherein this respiratory motion sensor and electrocardiography electrodes are used for assigning to each event detected during a single photon emission computed tomography (SPECT) process a certain respiratory phase and a certain cardiac phase and wherein for each combination of a respiratory phase and a cardiac phase a SPECT image is reconstructed. Images of the plurality of SPECT images, which have a common cardiac phase and different respiratory phases, are transformed into a series of respiratory compensated images at the plurality of cardiac phases and at a selected common respiratory phase.
  • SPECT single photon emission computed tomography
  • the series of respiratory compensated images is transformed in accordance with a heart shape and motion model to generate a series of cardiac and respiratory compensated images in a selected common cardiac phase and the selected common respiratory phase, wherein then the images in the selected common cardiac and respiratory phases are combined
  • positron emission tomography (PET) and computed tomography (CT) systems generate a CT image, which is used together with acquired PET raw data for reconstructing an attenuation corrected (AC) PET image.
  • CT computed tomography
  • respiratory motion can lead to a blurring in the reconstructed AC PET image and to an incorrect attenuation correction, thereby reducing the quality of the reconstructed AC PET image.
  • a motion compensation technique can be used, which splits the breathing cycle into a predetermined, small number of respiratory phases, using an external respiratory gating device like a respiratory belt for tracking the respiratory phase.
  • the quality of the motion compensation technique relies on a stable correlation between the tracking signal generated by the external gating device and the respiratory phase, which is very difficult to achieve.
  • the correlation between the tracking signal and the respiratory phase has therefore often a relatively low accuracy, which reduces the quality of determining respiratory phases and, thus, the quality of reconstructing a PET image based on the determined respiratory phases.
  • a respiratory motion determination apparatus for determining respiratory motion of a living being is presented, wherein the respiratory motion determination apparatus comprises:
  • the respiratory motion determination unit determines the respiratory motion of the living being based on the structure, which is influenced by cardiac motion and by respiratory motion and which is detected in the intermediate images, which have been reconstructed from the raw data assigned to different times, the respiratory motion can be determined, without relying on a stable correlation between a tracking signal of an external respiratory gating device and respiratory phases. This allows determining respiratory motion with high accuracy, which in turn allows improving a motion compensation technique for reconstructing a respiratory motion compensated image.
  • the structure is preferentially a structure of the heart.
  • the respiratory motion of the living being can be the respiratory motion of any part of the living being, i.e. the respiratory motion is the respiratory motion of at least a part of the living being.
  • the determined respiratory motion is the respiratory motion of the entire lung or of a part of the lung.
  • the determined respiratory motion can also be the respiratory motion of the entire heart or the respiratory motion of the structure.
  • the raw data providing unit can be a raw data acquisition unit like a PET data acquisition unit, a SPECT data acquisition unit, et cetera.
  • the raw data providing unit can also be a storing unit, in which the raw data are stored already and from which the raw data can be retrieved for providing the same.
  • the raw data providing unit can also be a receiving unit for receiving the raw data via a wireless or wired data connection from, for example, an imaging modality, wherein the raw data providing unit can be adapted to provide the received raw data.
  • the respiratory motion determination apparatus can therefore be, for example, a computer system comprising at least the raw data providing unit, the reconstruction unit, the structure detection unit and the respiratory motion determination unit, or the respiratory motion determination apparatus can be an imaging system, wherein the raw data providing unit can be a raw data acquisition unit.
  • the living being is a person or an animal.
  • the respiratory motion determination apparatus further comprises:
  • the intermediate image of a group can therefore be regarded as being an image comprising averaged information, wherein the average is performed over a single heart cycle.
  • the resulting intermediate images are independent of cardiac phases, but still dependent on respiratory motion.
  • the respiratory motion determination unit can therefore determine the respiratory motion of the living being independent of the heart beats, thereby further improving the quality of determining the respiratory motion.
  • the raw data providing unit is adapted to provide nuclear raw data as the raw data.
  • the raw data providing unit is adapted to provide PET data as the raw data.
  • the cardiac signal providing unit is preferentially adapted to provide an electrocardiogram signal (ECG) as the cardiac signal.
  • ECG electrocardiogram signal
  • the heart cycles are preferentially identified in the ECG signal by automatically determining QRS complexes from the ECG signal, wherein the determined QRS complexes are used to split the raw data into segments corresponding to the heart cycles by using, for example, the R peaks.
  • a time segment which corresponds to a heart cycle and which is used for grouping the raw data, is defined by an R-to-R segment of the ECG signal.
  • the reconstruction unit uses then the raw data, in particular, the PET count/events within a time segment for reconstructing an intermediate image for this time segment, i.e. for a group of raw data, which have timestamps within the respective time segment.
  • the structure detection unit is adapted to detect the heart muscle as the structure.
  • the structure detection unit is adapted to detect the apex of the heart muscle as the structure.
  • the heart muscle in particular, the apex of the heart muscle, is generally well detectable in the intermediate images, thereby allowing a high quality detection of the structure, which is used for determining the respiratory motion.
  • the intermediate images are non-attenuation corrected (NAC) PET images
  • NAC non-attenuation corrected
  • the heart muscle is clearly visible and of much greater intensity then, for example, lung or liver structures.
  • the heart since the heart resides directly on top of the diaphragm, its motion is a direct measure of the respiratory motion.
  • the apex of the heart muscle as a structure for determining the respiratory motion can therefore further improve the quality of determining the respiratory motion.
  • the respiratory motion determination unit is adapted to determine the positions of the structure in the reconstructed intermediate images as the respiratory motion of the living being and to determine for each reconstructed intermediate image the respective respiratory phase of the living being depending on the positions of the structure detected in the reconstructed intermediate images.
  • the respiratory motion determination apparatus comprises a respiratory phase image set providing unit for providing a respiratory phase image set of the living being, wherein the respiratory motion image set comprises for different respiratory phases different images of the structure, wherein the respiratory motion determination unit is adapted to determine the respiratory phase of a reconstructed intermediate image by comparing the position of the structure in the reconstructed intermediate image with the position of the structure in the respiratory phase image set.
  • the respiratory phase determination unit is adapted to determine the respiratory phase of a reconstructed intermediate image by determining the image of the provided respiratory phase image set showing the structure with a smallest distance to the structure shown in the reconstructed intermediate image and by determining the respiratory phase of the determined image of the respiratory phase image set with the smallest distance as the respiratory phase of the reconstructed intermediate image.
  • the respiratory phase image set is preferentially a multi-phase CT image or a multi-phase MR image of the living being, wherein the respiratory phase image comprises several CT or MR images for different respiratory phases and wherein a respiratory phase is determined for an intermediate image, in particular, for an intermediate PET image, by determining the CT or MR image with shortest distance between the apex position in the respective intermediate image and the apex position in the respective CT or MR image, wherein the respiratory phase of the respective CT or MR image with the shortest distance is determined as the respiratory phase of the respective intermediate image.
  • the respiratory motion determination apparatus comprises a respiratory motion model providing unit for providing a respiratory motion model of the living being, wherein the respiratory motion model provides for different respiratory phases different positions of the structure to be detected, wherein the respiratory motion determination unit is adapted to determine the respiratory phase of a reconstructed intermediate image by comparing the position of the structure in the reconstructed intermediate image with the position of the structure in the respiratory motion model. Preferentially, the respiratory motion model and the respective reconstructed intermediate image are aligned before determining the respiratory phase.
  • the respiratory motion model can also model anatomical features like the pleura, the apex of the lungs, the tips of the lungs, the diaphragm, et cetera, wherein these anatomical features can be used for aligning the respiratory motion model with the respective reconstructed intermediate image.
  • This allows determining the respiratory phase for the different reconstructed intermediate images, without using a patient-specific respiratory phase image like a multi-phase CT image or a multi-phase MR image.
  • this motion model can be obtained from a mean or patient-group specific average of CT or MR images of the respiratory motion, or from a simple geometric model of the torso and the respiratory motion.
  • the respiratory motion determination unit is adapted to fit a trajectory to the respiratory movement of the structure and to determine respiratory phases based on the fitted trajectory, thereby defining respiratory phases for the reconstructed intermediate images. This allows determining the respiratory phases just based on the reconstructed intermediate images, without needing, for example, a respiratory phase image like a multi-phase CT or MR image, or a respiratory motion model.
  • the reconstruction unit is further adapted to reconstruct an image of the living being based on the determined respiratory phases.
  • the reconstruction unit can be adapted to reconstruct for different respiratory phases different respiratory phase images based on the raw data of the respective respiratory phase.
  • a respiratory phase image can be determined directly from the raw data of the respective phase or by averaging the reconstructed intermediate images of the same respective respiratory phase.
  • the respiratory cycle is divided into a number of respiratory intervals defining a corresponding number of respiratory phases.
  • the respiratory cycle can be divided into ten respiratory intervals defining ten respiratory phases.
  • the intermediate images, which correspond to the same respiratory interval, are regarded as having the same respiratory phase.
  • a respiratory phase image is reconstructed based on the image raw data, which correspond to the respective respiratory interval.
  • reconstructed intermediate images, which correspond to the same respiratory interval are averaged for producing a respiratory phase image for the respiratory interval, i.e. for the respiratory phase defined by the respiratory interval.
  • the different respiratory intervals can have the same length, i.e.
  • the respiratory phases can be equidistant, or the respiratory intervals can have different lengths, i.e. the respiratory phases may not be equidistant.
  • the lengths of the respiratory intervals can be a posteriori defined based on the motion states of the structure from the reconstructed intermediate images. For example, from the reconstructed intermediate images, i.e. from the movement of the structure, the end inhale state and the end exhale state can be determined, wherein respiratory intervals, which are centered on the end inhale state and end exhale state, can be defined such that they have a larger length than respiratory intervals between these states.
  • the raw data are nuclear raw data
  • the reconstructed intermediate images are reconstructed nuclear images
  • the respiratory motion determination apparatus further comprises a respiratory phase image set providing unit for providing a respiratory phase image set of the living being, wherein the respiratory phase image set comprises for different respiratory phases different attenuation images of the living being, and wherein the reconstruction unit is further adapted to attenuation-correct the different nuclear respiratory phase images based on the determined respiratory phases and the provided respiratory phase image set.
  • the attenuation correction of the individual nuclear respiratory phase images improves the quality of these images.
  • the raw data are nuclear raw data
  • the reconstructed intermediate images are reconstructed nuclear images
  • the respiratory motion determination apparatus comprises a) a respiratory motion model providing unit for providing a respiratory motion model of the living being, wherein the respiratory motion model provides for different respiratory phases different positions of the structure of the heart, and b) a static attenuation image providing unit for providing a static attenuation image, wherein the reconstruction unit is adapted to i) deform the static attenuation image in accordance with the provided respiratory motion model for producing different attenuation images for different respiratory phases, and ii) attenuation-correct each reconstructed intermediate image based on the attenuation image produced for the respiratory phase of the respective reconstructed intermediate image.
  • the provided static attenuation image can be a static attenuation image of the living being, which is or which is based on, for example, a CT image of the living, or the provided static attenuation image is not based on the specific actual living being, but, for instance, an average of attenuation images of different persons, wherein each of these attenuation images may be reconstructed from raw data corresponding to a certain respiratory phase or to an entire respiratory cycle.
  • the reconstruction unit is adapted to register the different respiratory phase images and to average the registered respiratory phase images for producing a static image.
  • the respiratory motion determination apparatus can comprise an attenuation image providing unit for providing an attenuation image of the object, wherein the reconstruction unit is adapted to attenuation correct the static image based on the provided attenuation image.
  • the provided attenuation image is preferentially a static attenuation image.
  • the reconstruction unit is adapted to reconstruct a respiratory motion compensated image from the raw data and the determined respiratory motion.
  • the reconstruction unit can be adapted to reconstruct the respiratory motion compensated image directly from the raw data or indirectly from the raw data, i.e. by using, for instance, intermediate motion state images, which can then be combined in accordance with the determined respiratory motion.
  • the raw data can be grouped into a number of groups, for example, into 10 groups, defining a number of motion states, wherein for each group a motion state image can be reconstructed based on the raw data of the respective group.
  • the respiratory motion compensated image can, for example, be attenuation corrected by using a corresponding attenuation map.
  • a respiratory motion model can be provided, which describes the respiratory motion of an entire thorax region of the living being depending on the determined respiratory motion of the structure, in particular, depending on the respiratory motion of the apex of the heart muscle.
  • this respiratory motion model can define the displacements of different lung regions with respiratory motion.
  • the respiratory motion of the entire thorax portion together with the raw data can then be used for reconstructing a respiration compensated image of at least a part of the thorax.
  • raw data corresponding to the same position of the structure and, thus, to the same respiratory motion state can be used for reconstructing motion state images, which can then be combined in accordance with the respiratory motion model for reconstructing a motion compensated image.
  • the raw data can be corrected for respiratory motion by using the determined respiratory motion of the entire thorax, wherein then the motion corrected raw data can be reconstructed for generating a respiratory motion compensated image. For instance, if the raw data are PET data, each corresponding line-of-response can be shifted in accordance with the determined respiratory motion of the entire thorax.
  • a respiratory motion determination method for determining respiratory motion of a living being comprising:
  • a computer program for determining respiratory motion of a living being comprises program code means for causing a respiratory motion determination apparatus as defined in claim 1 to carry out the steps of the respiratory motion determination method as defined in claim 12, when the computer program is run on a computer controlling the respiratory motion determination apparatus.
  • Fig. 1 shows schematically and exemplarily a respiratory motion determination apparatus for determining respiratory motion of a living being.
  • the respiratory phase determination apparatus 1 is a PET imaging system, which can be adapted to determine respiratory motion of a person 3 lying on a table 4 and to use the determined respiratory motion together with acquired PET raw data for reconstructing a PET image.
  • the respiratory motion determination apparatus 1 comprises a raw data providing unit 2 for providing raw data assigned to different times, wherein the raw data are indicative of a structure of the heart of the person 3 and usable for reconstructing an image of the structure of the heart, and wherein the structure of the heart is influenced by respiratory motion.
  • the raw data providing unit 2 is a PET raw data acquisition unit for acquiring PET raw data.
  • the PET raw data are individual PET events or PET counts and are provided together with their respective acquisition times, i.e. with their timestamps.
  • the respiratory motion determination apparatus further comprises a cardiac signal providing unit 11 for providing a cardiac signal at the different times to which the raw data are assigned, wherein the cardiac signal is indicative of heart cycles.
  • the cardiac signal is preferentially an ECG signal, which is temporally correlated with the timestamps of the PET raw data.
  • the respiratory motion determination apparatus 1 further comprises a raw data grouping unit 5 for grouping raw data of a same heart cycle in a group based on the provided cardiac signal, wherein the reconstruction unit 6 is adapted to reconstruct an intermediate image for each group depending on the raw data of the respective group.
  • heart cycles can be identified in the ECG signal by automatically determining QRS complexes from the ECG signal.
  • Fig. 2 shows schematically and exemplarily such an ECG signal 16 having a QRS complex between the lines 14.
  • the QRS complex is usually the central and most visually obvious part the ECG signal 16.
  • the QRS generally includes the R-peak 15 of the ECG signal 16.
  • the raw data grouping unit 5 is preferentially adapted to split the raw data into segments corresponding to the heart cycles by using the R-peaks.
  • a time segment which corresponds to a heart cycle and which is used for grouping the raw data, is defined by an R-to-R segment of the ECG signal 16.
  • All raw data belonging to the same R-to-R segment of the ECG signal 16 are preferentially grouped into a same group.
  • the resulting intermediated images can be regarded as being a kind of average over a heart cycle such that the intermediated images are independent of cardiac phases, but still depending on respiratory phases.
  • the respiratory motion determination apparatus 1 further comprises a structure detection unit 7 for detecting the structure of the heart in the reconstructed intermediate images.
  • the structure detection unit 7 is adapted to detect the apex of the heart muscle as the structure of the heart.
  • Fig. 3 shows schematically and exemplarily an intermediate image being a PET image 17 of the person 3.
  • the heart muscle 18 and the apex 19, which is indicated by a cross, can clearly be identified as being the structure with the highest activity in this example.
  • the structure detection unit 7 detects therefore preferentially the heart muscle in the reconstructed intermediate images, followed by a detection of the apex.
  • the respiratory phase determination apparatus 1 further comprises a respiratory motion determination unit 10 for determining the respiratory motion of the living being based on the structure detected in the reconstructed intermediate images.
  • the respiratory motion determination unit 10 is adapted to determine the positions of the structure in the reconstructed intermediate images as the respiratory motion of the structure and to determine for each reconstructed intermediate image the respective respiratory phase of the person 3 depending on the positions of the structure detected in the reconstructed intermediate images.
  • the respiratory phase determination apparatus 1 can comprise a respiratory phase image set providing unit 8 for providing a respiratory phase image set of the heart, wherein the respiratory phase image set comprises for different respiratory phases different images of the heart and wherein the respiratory motion determination unit 10 is adapted to determine the respiratory phase of a reconstructed intermediate image by comparing the position of the structure in the reconstructed intermediate image with the position of the structure in the respiratory phase image set.
  • the respiratory motion determination unit 10 is adapted to determine the respiratory phase of a reconstructed intermediate image by determining the image of the provided respiratory phase image set showing the structure with the smallest distance to the structure shown in the reconstructed intermediate image and by determining the respiratory phase of the determined image of the respiratory phase image set with the smallest distance as the respiratory phase of the reconstructed intermediate image.
  • the respiratory phase image set can be a multi-phase CT image or a multi-phase MR image set, wherein the respiratory phase image set comprises several CT or MR images for different respiratory phases and wherein a respiratory phase is determined for an intermediate PET image by determining the CT or MR image showing the apex position with the shortest distance to the apex position shown in the respective intermediate PET image.
  • the respiratory phase of the respective CT or MR image with the shortest distance is then determined as the respiratory phase of the respective intermediate PET image.
  • the respiratory phase image set can also be a multi-phase attenuation image set, which may be based on a multi-phase MR image set or a multi-phase CT image set or which may directly be a multi-phase CT image set.
  • the multi-phase attenuation image set comprises for different respiratory phases different attenuation images, wherein different regions of the attenuation images representing different elements of the living being, in particular, different tissue types, comprise different corresponding attenuation values.
  • the respiratory cycle is divided into a certain number of respiratory segments, wherein each respiratory segment defines a respiratory phase.
  • ten respiratory phases can be defined by dividing the respiratory cycle into ten respiratory segments.
  • the reconstruction unit 6 is preferentially adapted to reconstruct for each of the respiratory phases, i.e. for each of the respiratory segments, a respiratory phase image based on the raw data of the respective respiratory phase.
  • the reconstruction unit 6 can be adapted to use directly the raw data of the respective respiratory phase for generating a respiratory phase image being, in this embodiment, a respiratory phase NAC PET image, or the reconstruction unit 6 can be adapted to average the reconstructed intermediate NAC PET images of a same respective respiratory phase for producing for the respective respiratory phase a respiratory phase NAC PET image.
  • the respiratory phase image set providing unit 8 is adapted to provide attenuation images of the living being for different respiratory phases bases on, for example, corresponding multi-phase CT or MR images
  • the reconstructing unit 6 is adapted to attenuation-correct the different respiratory phase PET images based on the determined respiratory phases and the corresponding attenuation images of the living being.
  • the reconstruction unit 6 is preferentially adapted to register the different attenuation-corrected respiratory phase PET images and to average the registered respiratory phase PET images for producing a static image.
  • the attenuation-corrected respiratory phase PET images can be aligned by a rigid, affine or elastic registration, or by any other suitable registration method, and the aligned respiratory phase PET images can be averaged for producing a "freezed" NAC PET image which is compensated for respiratory motion.
  • the reconstruction unit can also be adapted to firstly register the NAC respiratory phase PET images and to average the NAC respiratory phase PET images for producing a static NAC PET image, wherein then the NAC respiratory phase PET image can be corrected by using a corresponding attenuation image.
  • the respiratory motion determination apparatus 1 can comprise an attenuation image providing unit 12 for providing a static attenuation image of the living being, wherein the reconstruction unit 6 can be adapted to attenuation correct the static NAC PET image based on the provided static attenuation image.
  • the raw data grouping unit 5, the reconstruction unit 6, the structure detection unit 7, the respiratory phase image set providing unit 8, the respiratory motion model providing unit 9, the respiratory motion determination unit 10 and the static attenuation image providing unit 12 can be regarded as being part of a processing device 20, which may be a computer, for processing the raw data.
  • the one or several reconstructed images can be shown on a display 13.
  • At least the final reconstructed images show preferentially not only the structure of the heart, but also at least one object of interest like a tumor to be investigated.
  • the provided raw data are therefore preferentially not only indicative of the structure of the heart, but also of an object of interest which is influenced by respiratory motion.
  • the structure of the heart is used for determining the respiratory motion, wherein the determined respiratory motion is then used for reconstructing an image of the object of interest using the determined respiratory motion.
  • the respiratory motion determination apparatus 1 can further be adapted to determine the respiratory phases of the living being based on the structure detected in the reconstructed intermediate images in another way.
  • the respiratory motion determination apparatus can further comprise a respiratory motion model providing unit 9 for providing a respiratory motion model of the living being, wherein the respiratory motion model provides for different respiratory phases different positions of the structure of the heart and wherein the respiratory motion determination unit 10 is adapted to determine the respiratory phase of a reconstructed intermediate image by comparing the position of the structure in the reconstructed intermediate image with the position of the structure in the respiratory motion model.
  • the apex position of the heart muscle is mapped to the respiratory motion model for determining for each reconstructed intermediate image a respective respiratory phase.
  • the attenuation image providing unit 12 can then provide a static attenuation image of the living being, which can be deformed by the reconstruction unit 6 in accordance with the provided respiratory motion model for producing different attenuation images for different respiratory phases.
  • the attenuation image comprises for different elements of the living being like different kinds of tissue different attenuation values, wherein the reconstruction unit 6 can be adapted to attenuation-correct each reconstructed intermediate image based on the attenuation image produced for the respiratory phase of the respective reconstructed intermediate image by the above mentioned deformation of the static attenuation image.
  • these attenuation-corrected intermediate images can be averaged for producing respiratory phase images, wherein a respiratory phase image is the average of the attenuation-corrected intermediate images assigned to the same respective respiratory phase.
  • the resulting attenuation-corrected respiratory phase images in particular, the AC respiratory phase PET images, can be registered and averaged for producing a static image which is compensated for respiratory motion.
  • the produced respiratory phase images or the optional static image can be attenuation-corrected.
  • a respiratory phase image can be reconstructed by directly using the raw data, which correspond to the intermediate images of the respective same respiratory phase.
  • the respiratory motion determination apparatus can be adapted to allow determining the respiratory phases of the living being in a further other way.
  • the detected structure of the heart in the different reconstructed intermediate images defines a movement of the structure
  • the respiratory motion determination unit 10 can be adapted to fit a trajectory to the movement of the structure and to determine the respiratory phases based on the fitted trajectory, thereby defining respiratory phases for the reconstructed intermediate images.
  • the apex positions of the heart muscle from all reconstructed intermediate PET images are collected and the trajectory is fitted to a superposition or overlay of all apex positions shown in the different reconstructed intermediate PET images.
  • the fitted trajectory describes, for example, a back and forth movement of the apex position along a line or an ellipse.
  • the respiratory phases are preferentially determined based on the fitted trajectory by subdividing the trajectory into a number of boxes or intervals.
  • the trajectory can be subdivided into ten boxes or intervals, in order to define ten respiratory phases.
  • each reconstructed intermediate image is assigned to a respiratory phase by determining in which of the boxes or intervals the apex position of the respective intermediate image is located.
  • a respiratory phase image in this embodiment, a respiratory phase PET image, can then be determined by averaging the intermediate images assigned to the same respiratory phase or by directly using the underlying raw data for reconstructing a respiratory phase image for the respective respiratory phase.
  • the respiratory phase images can then be aligned with respect to each other as described above by using, for example, a rigid, affine or elastic registration, wherein the aligned respiratory phase images can be averaged for determining a single static image which is compensated for respiratory motion.
  • the static image can be attenuation corrected by using a single static attenuation map, which may be based on a CT or MR image, or the intermediate or respiratory phase images can be attenuation corrected, before generating the static image which is compensated for respiratory motion.
  • raw data are provided, which are assigned to different times, wherein the raw data are indicative of a structure of the heart of the living being and useable for reconstructing an image of the structure of the heart, wherein the structure of the heart is influenced by respiratory motion, by the raw data providing unit 2.
  • PET data are acquired by the PET data acquisition unit 2, wherein the PET data, i.e. the PET counts or events, are time stamped.
  • the cardiac signal providing unit 11 provides a cardiac signal at the different times to which the raw data are assigned, wherein the cardiac signal is indicative of the heart cycles.
  • an ECG signal is acquired, while the PET data are acquired.
  • the reconstruction unit 6 reconstructs intermediate images which show at least the structure being, in this embodiment, the apex of the heart muscle from the provided raw data.
  • the raw data grouping unit 5 groups raw data of a same heart cycle in a group based on the provided cardiac signal and the reconstruction unit 6 reconstructs an intermediate image for each group depending on the raw data of the respective group.
  • the structure detection unit 7 detects the structure in the reconstructed intermediate images
  • the respiratory phase determination unit 10 determines the positions of the structure in the reconstructed intermediate images as respiratory motion of the living being and determines the respiratory phases of the living being based on the positions of the structure detected in the reconstructed intermediate images.
  • the respiratory phase of the living being is determined depending on the positions of the structure detected in the reconstructed intermediate images.
  • a respiratory phase can be determined for a reconstructed intermediate image by comparing the position of the structure in the reconstructed intermediate image with the position of the structure in a respiratory phase image set, which comprises for different respiratory phases different images of the living being showing the position of the structure in the respective respiratory phase.
  • the respiratory phase of a reconstructed intermediate image can be determined by comparing the position of the structure in the reconstructed intermediate image with the position of the structure in a respiratory motion model, wherein the respiratory motion model provides for different respiratory phases different positions of the structure. It is also possible to fit a trajectory to the movement of the structure detected in the intermediate images and to determine the respiratory phases based on the fitted trajectory as described above.
  • the reconstruction unit 6 reconstructs for different respiratory phases different respiratory phase images based on the raw data of the respective respiratory phase. This reconstruction can be performed directly on the raw data of the respective phase or by averaging the reconstructed intermediate images of the same respective respiratory phase.
  • the respiratory phase images are attenuation corrected by using, for example, a respiratory phase dependent attenuation image, i.e. different attenuation images for different respiratory phases, wherein an attenuation image comprises for different element of the living being, in particular, for different types of tissue, different attenuation values.
  • a respiratory phase dependent attenuation image i.e. different attenuation images for different respiratory phases
  • an attenuation image comprises for different element of the living being, in particular, for different types of tissue, different attenuation values.
  • step 107 the attenuation-corrected respiratory phase images can be registered and averaged to generate an attenuation-corrected static image which is compensated for respiratory motion.
  • the respiratory phase determination apparatus can be used for PET/CT imaging or PET/MR imaging.
  • PET/CT imaging and PET/MR imaging have a tremendous impact on cancer management, because they do not only enable detection of tumors, but also allows for differential diagnoses.
  • PET/CT imaging and PET/MR imaging can be used, for example, for the quantitative estimation of tumor response to therapy.
  • Respiratory motion can generally limit the utility of PET/CT imaging and PET/MR imaging, on one hand due to blurring and on the other hand due to incorrect attenuation correction. Blurring can cause an overestimation of tumor volume and/or underestimation of tracer uptake.
  • Incorrect attenuation correction can lead to an underestimation of tracer uptake, in particular, if the tumor is located close to an organ boundary with a distinctive change in attenuation, such as the lungs.
  • An attenuation map i.e. an attenuation image, for attenuation correction can be derived from a CT image, in particular, a low-resolution CT image, and its segmentation into different elements of the living being like air, fat, muscle, lungs et cetera.
  • An MR image can also be segmented in a similar fashion and used for creating the attenuation map.
  • the attenuation map can be a static attenuation map or it can be a multi-phase attenuation map, which may be based on a multi-phase CT or MR image, respectively.
  • a multi-phase attenuation map offers a phase-matched attenuation correction such that in an ideal case each, for example, PET count, can be corrected for attenuation with respect to its underlying anatomy, and summed at a position consistent with the anatomy.
  • Current motion compensation techniques split the respiratory cycle into a predetermined, small number of, for example, ten respiratory phases by using an external gating device like a respiratory belt to track the respiratory phases and to create gated reconstructions within time windows, which correspond to the respiratory phases.
  • Each of these reconstructed images then corresponds to an individual phase of the respiratory cycle, and can be overlaid correctly by using a respiratory model derived from, for example, a lung segmentation in a multi-phase CT or MR image.
  • This gating relies on a stable correlation between the tracking signal and the respiratory state, which is very difficult to achieve even with visual feedback systems, in particular, audio-visual feedback systems, and even if the feedback systems are optimally placed.
  • the respiratory phase determination apparatus is therefore preferentially adapted to use respiration-induced heart motion as an anatomical image-based tracker for determining the respiratory phase.
  • respiration-induced heart motion In particular in PET images the heart muscle is clearly visible and of much greater intensity then, for example, lung or liver structures. Since the heart resides directly on top of the diaphragm, its motion is a direct measure of the respiratory state. However, the respiration-induced motion of the heart is overlaid with its beating motion. Typically, an adults heart at rest beats 40 to 80 times per minute, thus a heart cycle is completed after about 1 second. A breathing cycle takes typically 10 to 15 seconds. Averaging the heart motion of one heart beat determines the mean respiratory state during the corresponding interval. This can be used to look up the correct anatomical phase both for the attenuation correction and for the anatomically consistent overlay of the reconstructed image.
  • the cardiac signal is an ECG signal
  • the cardiac signal can also be any other signal being indicative of the heart cycles.
  • a heart beat sensor attached to a person's wrist can be used, which measures the heart cycle depending on, for example, a pulse measurement.
  • the respiratory phase determination apparatus can be adapted to determine the respiratory phases from images generated by other imaging modalities like SPECT images, CT images, MR images, ultrasound images, et cetera.
  • the respiratory motion determination apparatus can also be adapted to determine respiratory motion of the living being based on the structure detected in the intermediate images, without necessarily determining respiratory phases, wherein the determined respiratory motion together with the raw data can be used to reconstruct a respiratory motion compensated image.
  • a respiratory motion model can be provided, which describes the respiratory motion of an entire thorax region of the living being depending on the determined respiratory motion of the structure, in particular, depending on the respiratory motion of the apex of the heart muscle.
  • the respiratory motion of the entire thorax portion together with the raw data can then be used for reconstructing a respiration compensated image of at least a part of the thorax.
  • raw data corresponding to the same position of the structure and, thus, to the same respiratory motion state can be used for reconstructing motion state images, which can then be combined in accordance with the respiratory motion model for reconstructing a motion compensated image.
  • the raw data can be corrected for respiratory motion by using the determined respiratory motion of the entire thorax, wherein then the motion corrected raw data can be reconstructed for generating a respiratory motion compensated image. For instance, if the raw data are PET data, each corresponding line-of-response can be shifted in accordance with the determined respiratory motion of the entire thorax.
  • the respiratory phase determination apparatus and method can be adapted to be used in a PET system, in particular, a time of flight PET system, a PET/CT system, a PET/MR system et cetera, especially for tumor response assessment in the thorax, in particular, in the lungs.
  • a single unit or device may fulfill the functions of several items recited in the claims.
  • the mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage.
  • Calculations like the calculations performed for reconstructing images, determining phases of the reconstructed images and correcting the images with respect to attenuation, et cetera performed by one or several unit or devices can be performed by any other number of units or devices.
  • steps 101 to 107 can be performed by a single unit or by any other number of different units.
  • the calculation and/or the control of the respiratory motion determination apparatus in accordance with the respiratory motion determination apparatus can be implemented as program codes means of a computer program and/or as dedicated hardware.
  • a computer program may be stored/distributed on a suitable medium, such as an optical storage medium or a solid-state medium, supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems.
  • a suitable medium such as an optical storage medium or a solid-state medium, supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the Internet or other wired or wireless telecommunication systems.
  • the invention relates to a respiratory motion determination apparatus for determining respiratory motion of a living being.
  • a raw data providing unit provides raw data assigned to different times, wherein the raw data are indicative of a structure like the apex of the heart muscle, which is influenced by cardiac motion and by respiratory motion, and a reconstruction unit reconstructs intermediate images of the structure from the provided raw data.
  • a structure detection unit detects the structure in the reconstructed intermediate images, and a respiratory motion determination unit determines the respiratory motion of the living being based on the structure detected in the reconstructed intermediate images. This allows determining respiratory motion with high accuracy, without relying on, for example, a stable correlation between a tracking signal of an external respiratory gating device and respiratory phases.

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Families Citing this family (38)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9305377B2 (en) * 2011-01-05 2016-04-05 Koninklijke Philips N.V. Method and apparatus to detect and correct motion in list-mode PET data with a gated signal
DE102012213551A1 (de) * 2012-08-01 2014-02-06 Siemens Aktiengesellschaft Verfahren zur bewegungsgemittelten Schwächungskorrektur und Magnetresonanz-Anlage
US9400317B2 (en) * 2012-12-04 2016-07-26 Siemens Medical Solutions Usa, Inc. MR scan selection for PET attenuation correction
EP2982304B1 (en) * 2013-04-05 2018-04-25 Toshiba Medical Systems Corporation Medical image processing apparatus and medical image processing method
CN103536282B (zh) * 2013-11-06 2015-02-04 中国人民解放军第三军医大学 基于Fast-ICA法的磁感应心肺活动信号分离方法
JP6425885B2 (ja) * 2013-12-20 2018-11-21 キヤノンメディカルシステムズ株式会社 核医学診断装置、画像処理装置および画像処理プログラム
JP6273940B2 (ja) * 2014-03-19 2018-02-07 コニカミノルタ株式会社 画像解析装置、画像撮影システム及び画像解析プログラム
DE102014209437B3 (de) * 2014-05-19 2015-10-22 Sirona Dental Systems Gmbh Verfahren zur Erzeugung magnetresonanztomographischer Aufnahmen von zyklischer Bewegung
DE102014216023A1 (de) * 2014-08-13 2016-03-03 Siemens Aktiengesellschaft Verfahren und Vorrichtung zur Überlagerung eines 3D-Bilddatensatzes in einem 2D-Bild mit Atmungsbewegungskompensation
US9526468B2 (en) * 2014-09-09 2016-12-27 General Electric Company Multiple frame acquisition for exposure control in X-ray medical imagers
CN104287769B (zh) * 2014-10-13 2016-10-05 沈阳东软医疗系统有限公司 一种基于pet/ct设备的外部门控信号检测装置及方法
DE102014225282B4 (de) * 2014-12-09 2016-07-21 Siemens Healthcare Gmbh Deformationsberechnung bei zyklischer Bewegung eines Untersuchungsobjekts
CN107209241B (zh) * 2015-02-06 2020-02-07 皇家飞利浦有限公司 磁共振图像的自动分组
JP6348865B2 (ja) * 2015-03-30 2018-06-27 株式会社リガク Ｃｔ画像処理装置および方法
US10255684B2 (en) * 2015-06-05 2019-04-09 University Of Tennessee Research Foundation Motion correction for PET medical imaging based on tracking of annihilation photons
DE102015215584B4 (de) * 2015-08-14 2022-03-03 Siemens Healthcare Gmbh Verfahren und System zur Rekonstruktion von Planungsbildern
US11633166B2 (en) * 2015-09-23 2023-04-25 Siemens Medical Solutions Usa, Inc. Spatial registration of positron emission tomography and computed tomography acquired during respiration
DE102015218819A1 (de) * 2015-09-30 2017-03-30 Siemens Healthcare Gmbh Verfahren und System zur Bestimmung einer Atemphase
EP3488782B1 (en) * 2016-07-19 2021-09-29 Paramevia Pte. Ltd. Diagnosis support program
CN109640824B (zh) * 2016-08-22 2023-06-30 皇家飞利浦有限公司 模型正则化运动补偿的医学图像重建
US10360724B2 (en) 2016-12-21 2019-07-23 Uih America, Inc. Methods and systems for emission computed tomography image reconstruction
US10255694B2 (en) * 2016-12-21 2019-04-09 Uih America, Inc. Methods and systems for emission computed tomography image reconstruction
WO2018172566A1 (en) * 2017-03-24 2018-09-27 Koninklijke Philips N.V. Noise-robust real-time extraction of the respiratory motion signal from pet list-data
US11410349B2 (en) 2017-03-24 2022-08-09 Koninklijke Philips N.V. Methods for data driven respiratory motion estimation
EP3382413B1 (de) * 2017-03-27 2022-08-10 Siemens Healthcare GmbH 2d navigatortechnik in der mrt
CN110536643B (zh) * 2017-04-21 2024-02-02 皇家飞利浦有限公司 用于断层摄影成像的使用脉搏血氧计的呼吸门控
US10282871B2 (en) 2017-07-10 2019-05-07 Shanghai United Imaging Healthcare Co., Ltd. Systems and methods for pet image reconstruction
US10690782B2 (en) * 2017-09-30 2020-06-23 Uih America, Inc. Systems and methods for positron emission tomography image reconstruction
EP3570060A1 (de) * 2018-05-15 2019-11-20 Siemens Healthcare GmbH Verfahren zur rekonstruktion von magnetresonanztomographie-aufnahmen mit variabler zeitauflösung
CN109965884A (zh) * 2019-04-19 2019-07-05 哈尔滨理工大学 一种基于加速度传感器的体表呼吸运动测量系统
US11492585B2 (en) * 2019-05-31 2022-11-08 Canon Medical Systems Corporation Cell identification system and cell identification method
CN110507343B (zh) * 2019-08-29 2023-08-01 上海联影医疗科技股份有限公司 运动场获取方法及pet图像校正方法、装置和计算机设备
US11367193B2 (en) * 2019-12-31 2022-06-21 Uih America, Inc. Systems and methods for medical imaging
US11806184B2 (en) 2020-04-13 2023-11-07 Delta Electronics, Inc. Method for gating in tomographic imaging system
TWI781575B (zh) * 2020-04-13 2022-10-21 台達電子工業股份有限公司 適用於斷層造影系統的門控方法
US11694374B2 (en) * 2020-04-13 2023-07-04 Delta Electronics, Inc. Method for gating in tomographic imaging system
KR102182665B1 (ko) * 2020-04-21 2020-11-25 주식회사 펜타드 무수축 몰탈의 공극 방지를 위한 교좌장치
CN113057665B (zh) * 2021-03-18 2022-03-18 上海卓昕医疗科技有限公司 肺部影像三维成像方法和系统

Family Cites Families (22)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5251128A (en) 1990-11-19 1993-10-05 General Electric Company Motion artifact reduction in projection imaging
US7756304B2 (en) * 1998-12-30 2010-07-13 Siemens Medical Solutions Usa, Inc. Medical diagnostic ultrasonic imaging method and system for displaying multi-phase, multi-frame images
JP3697233B2 (ja) * 2002-04-03 2005-09-21 キヤノン株式会社 放射線画像処理方法及び放射線画像処理装置
CN1809841B (zh) 2003-06-18 2010-05-12 皇家飞利浦电子股份有限公司 运动补偿的重建方法、设备与系统
US20050123183A1 (en) * 2003-09-02 2005-06-09 Paul Schleyer Data driven motion correction for nuclear imaging
US8285359B2 (en) 2003-11-26 2012-10-09 General Electric Company Method and system for retrospective gating using multiple inputs
EP1913421B1 (en) * 2005-08-04 2013-01-30 Koninklijke Philips Electronics N.V. Motion compensation in functional imaging
US8172756B2 (en) * 2005-10-20 2012-05-08 Koninklijke Philips Electronics N.V. Ultrasonic imaging system and method
JP2010501856A (ja) * 2006-08-22 2010-01-21 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 動きアーティファクト画像についてのアーティファクト補正
CN101622643B (zh) * 2007-03-02 2013-08-21 皇家飞利浦电子股份有限公司 心脏路图
FR2914176B1 (fr) * 2007-03-27 2009-05-22 Gen Electric Procede de detection et de compensation du mouvement respiratoire dans des images cardiaques fluoroscopiques synchronisees a un signal electrocardiogramme.
US9814431B2 (en) 2007-05-04 2017-11-14 Memorial Sloan Kettering Cancer Center Methods and systems for retrospective internal gating
JP5414157B2 (ja) * 2007-06-06 2014-02-12 株式会社東芝 超音波診断装置、超音波画像処理装置、及び超音波画像処理プログラム
JP5319157B2 (ja) * 2007-09-04 2013-10-16 株式会社東芝 超音波診断装置、超音波画像処理装置、及び超音波画像処理プログラム
US8391950B2 (en) * 2008-09-30 2013-03-05 Siemens Medical Solutions Usa, Inc. System for multi-dimensional anatomical functional imaging
US8175369B2 (en) * 2008-12-12 2012-05-08 Molecular Devices, Llc Multi-nucleated cell classification and micronuclei scoring
US8824756B2 (en) 2009-06-30 2014-09-02 University Of Utah Research Foundation Image reconstruction incorporating organ motion
CN101658426B (zh) 2009-09-11 2011-08-31 昆明理工大学 基于三维正电子发射探测器灵敏度特性的呼吸门控技术
CN101702232B (zh) 2009-10-16 2012-01-11 昆明理工大学 正电子发射成像中呼吸校正技术
RU2554378C2 (ru) * 2009-12-10 2015-06-27 Конинклейке Филипс Электроникс Н.В. Способ и устройство для использования времяпролетной информации для обнаружения и введения поправки на движение в сканограммах
WO2011073818A1 (en) * 2009-12-15 2011-06-23 Koninklijke Philips Electronics N.V. Motion compensation with tissue density retention
US8358738B2 (en) * 2010-08-27 2013-01-22 Elekta Ab (Publ) Respiration-correlated radiotherapy

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
None *

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